Method for treating neurovascular aneurysms

ABSTRACT

A graftless prosthetic stent for treatment of vascular lesions such as aneurysms and arterio-venous fistulas, especially in neurovascular vessels, comprises a continuous helical ribbon formed of a shape-retaining metal having a transition temperature at which the stent expands from its contracted condition to a radially expanded condition, the stent remaining substantially cylindrical in its contracted and expanded conditions. The helical windings have variable width, thickness, number or size of openings, or combinations of these features, which affect the stiffness, rate of expansion at the transition temperature, and the area of vessel wall covered by the stent. A catheter device which includes the stent, and a method of treatment using the stent are also provided.

The present application is related to U.S. provisional patentapplication Ser. No. 60/129,667 filed Apr. 15, 1999, and incorporatesthe application herein by reference.

FIELD OF THE INVENTION

The present invention relates to a vascular endoprosthesis, such as astent, for placement in an area of a body lumen that has been weakenedby damage or disease such as by aneurysm, and in particular, to a stentadapted for placement at a neurovascular site, and to a method of usingthe stent in treating a neurovascular aneurysm.

BACKGROUND OF THE INVENTION

Rupture of non-occlusive cerebrovascular lesions, such as intracranialsaccular aneurysms or arterio-venous fistulae, are a major cause ofstroke. Rupture of an aneurysm causes subarachnoid hemorrhage in whichblood from a ruptured vessel spreads over the surface of the brain.About 2.5% of the United States population (4 million Americans) have anunruptured aneurysm. About 100,000 of these people suffer a subarachnoidhemorrhage. The disease is devastating, often affecting healthy peoplein their 40's and 50's, with about half of the rupture victimssuccumbing within a month, and with half of the survivors becomingseriously disabled as a result of the initial hemorrhage or of a delayedcomplication.

Neurovascular arteries are generally quite small, having diametersranging from 2.0 to 4.0 mm in the Circle of Willis, 2.5 to 4.5 mm in thecavernous segment of the internal carotid artery, 1.5 to 3.0 mm invessels of the distal anterior circulation, and 2.0 to 4.0 mm in theposterior circulation. The incidence of aneurysm varies with thelocation, with 55% occurring in the Circle of Willis, 30% in theinternal carotid, 10% in the distal anterior circulation, and 5% in theposterior circulation.

Screening for these lesions and preventing rupture will lead to betterclinical outcomes and lower costs. Non-invasive treatments for rupturedand unruptured lesions are preferred over surgical interventions due tolower costs, lower mortality and morbidity, and patient preference. Anattractive treatment for ruptured and unruptured aneurysms is theplacement of a stent within the lumen to prevent rupture or re-ruptureof the lesion.

Stents formed of a helical coil or ribbon of shape-memory alloy materialare known in the art. In general, such stents are formed to a desiredexpanded shape and size for vascular use above the transitiontemperature of the material. The stent is then cooled below itstransition temperature and reshaped to a smaller-diameter coil suitablefor catheter administration. After the stent in its contracted,smaller-diameter shape is delivered to the target site, e.g., viacatheter, it is warmed by the body to above its transition temperature,causing the stent to assume its original expanded shape and size,typically a shape and size that anchors the stent against the walls ofthe vessels at the vascular site. Stents of this type are disclosed forexample, in U.S. Pat. Nos. 4,512,338, 4,503,569, 4,553,545, 4,795,485,4,820,298, 5,067,957, 5,551,954, 5,562,641, and 5,824,053. Also known inthe art are graft-type stents designed for treating aneurysms, typicallyat relatively large-vessel sites, e.g., with vessel lumen sizes betweenabout 15 and 30 mm. U.S. Pat. No. 4,512,338 is exemplary.

Stents such as disclosed heretofore have one or more of the followinglimitations, for purposes of the present invention:

(i) they are not capable of being advanced to a target site, such as aneurovascular site, that is accessible only along a tortuous path by asmall-diameter catheter;

(ii) they may cause vessel injury due to rapid expansion at the targetsite;

(iii) they are not suitable for treating aneurysms in the absence of aspecial graft, sleeve or webbing;

(iv) they may cause thrombosis (clotting) of small vessels with low flowsuch as neurovascular vessels.

It would therefore be desirable to provide a tent that overcomes theselimitations, and which is suitable, in one embodiment, for use intreating neuroaneurysms.

SUMMARY OF THE INVENTION

In one aspect, the invention includes a stent adapted for advancementthrough a catheter in a upstream to downstream direction to a targetvessel site, in a contracted stent condition, and expulsion from thecatheter, downstream end first, and radial expansion at the target site,to engage the walls of the vessel.

The stent is formed of a continuous helical ribbon, preferably formed ofa shape-memory alloy, and has a bending-stiffness gradient along itslength due to (i) a gradient of ribbon width, (ii) a gradient of ribbonthickness, and/or (iii) a gradient of size or number of openings formedin the stent ribbon. The stent has a preferred contracted-conditiondiameter of between about 10 and 30 mils, and a diameter in a fullyexpanded condition of between 40 and 125 mils.

In one general embodiment, the shape-memory alloy has a final austentitetransition temperature of between about 25° C. and 37° C. This featureallows the stent to be moved through the catheter in a martensitic,superelastic state, and to assume its preformed, austentitic shape whenexpelled from the catheter. In another embodiment, the shape-memoryalloy has a transition temperature M_(d), below which the alloy retainsstress-induced martensitic properties, of greater than 37° C. Thisallows the stent to be moved through the catheter in a stress-inducedmartensitic (SIM) state, and recover its preformed, austentite shapewhen released from the constraints of the catheter, at a temperaturethat may be substantially above the final austentite temperature. Inthis embodiment, the final austentite temperature may be quite low,e.g., 4° C., or it may be room temperature of higher.

The bending-stiffness gradient may be continuous along the length of thestent, or discontinuous, e.g., having two or more separate regions, eachwith substantially uniform stiffness. The stiffness gradient istypically greater stiffness upstream and lesser stiffness downstream, asthe stent is oriented in the catheter for delivery in anupstream-to-downstream direction.

Where the stiffness gradient is due to a gradient of ribbon width,greater ribbon width at the upstream end of the stent, and lesser ribbonwidth at the downstream end of the stent, the greater ribbon width ispreferably (i) at least ten times the ribbon thickness and (ii) at leasttwo times the lesser width. The greater ribbon width is effective toreduce the rate of expansion of the stent from its contracted to itsradially extended condition, relative to that of a stent having uniformwinding widths equal to the lesser ribbon widths, and to increase theangle of catheter bend through which the catheter can be advanced, in anupstream to downstream direction, relative to that of a stent havinguniform winding widths equal to the greater ribbon width. Preferably thegreater ribbon width is between 25 and 75 mils, and the lesser ribbonwidth, between 5 and 15 mils.

Where the stiffness gradient is due to a gradient of ribbon thickness,greater ribbon thickness at the upstream end of the stent, and lesserribbon thickness at the downstream end of the stent, the greater ribbonwidth is preferably in the range 1-4 mils, and the greater width,between 0.5 and 2 mils. Where the stent stiffness gradient is due tofewer or smaller openings formed along the length of the helical ribbon,greater opening area in a downstream direction, the openings arepreferably shaped and oriented to achieve greater stent flexibilitywhile preserving a real coverage of the target region. In one generalembodiment, the openings are I-beam shaped openings whose “I” axis isaligned transversely to the longitudinal axis of the stent in thecontracted state in another, they are Z-shaped openings whose centralaxis is aligned transversely to the longitudinal axis of the stent inthe contracted state. The helical ribbon is effective to cover between50% and 80% of the surface area of the vessel region containing thestent.

In a more specific embodiment, the invention includes a stent adaptedfor advancement through a catheter in a upstream to downstream directionto a target vessel site in a contracted stent condition, and withexpulsion from the catheter, downstream end first, and radial expansionat the target site, to engage the walls of the vessel. The stentincludes a continuous helical ribbon formed of a shape-memory metalhaving a ribbon thickness of 0.5 and 4 mils, and being effective tocover between 50% and 80% of the surface area of the vessel regioncontaining the stent. The stent has a bending-stiffness gradient alongits length due to (i) a gradient of ribbon width, (ii) a gradient ofribbon thickness; and/or a gradient of size or number of openings formedin the stent ribbon. The stent is characterized by acontracted-condition diameter of between about 10 and 30 mils, and adiameter in a fully expanded condition of between 40 and 125 mils.

In another aspect, the invention includes a catheter delivery devicehaving a catheter for accessing an intralumenal target site, a stent ofthe type described above, contained within the catheter in amartensitic, superelastic state, and a catheter pusher wire foradvancing the stent through the catheter in a downstream direction.

In still another aspect, the invention includes a method of treating alesion at a neurovascular target vessel site. The method includesguiding a neuro-interventional catheter to the target site, advancingthrough the catheter, a stent of the type described above, and expellingthe stent from the catheter at the target site, causing the stent toexpand radially against the vessel walls at the target site.

The step of guiding the stent to the target site may include engaging apusher wire releasably with the downstream end of the stent, pushing thestent through the catheter with the pusher wire, and expelling the stentfrom the catheter at the target site, with stent radial expansion at thetarget site being effective to release the stent from the pusher wire.The pusher wire can include a distal end ball adapted to be captured bythe stent, with such in its contracted condition. Alternatively, thepusher wire can include a distal notch adapted to be captured by thestent, with such in its contracted condition.

These and other objects and features of the invention will become morefully apparent when the following detailed description of the inventionis read in conjunction with the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a side view of a stent constructed in accordance with oneembodiment of the present invention, and shown in a contractedcondition;

FIG. 2 is a side view (2A) of a stent constructed in another embodimentof the present invention, and shown in a contracted condition (2B);

FIG. 3 is a cross-sectional view of the stent taken through line 3-3 inFIG. 1 that intersects an outer surface regions of stent;

FIG. 4 is a side view of the stent in FIG. 1, but shown in an expandedcondition;

FIG. 5 is a side view of a stent constructed in accordance with anotherembodiment of the present invention, and shown in a contractedcondition;

FIG. 6 is a side view of a stent constructed in accordance with a stillanother embodiment of the present invention, and shown in a contractedcondition;

FIG. 7 is a cross-sectional view of the stent taken through line 7-7 inFIG. 6 that intersects an outer surface regions of stent;

FIG. 8 is a side view of a stent constructed in accordance with a yetanother general embodiment of the present invention, and shown in acontracted condition;

FIG. 9 is a side view of a stent constructed in accordance with anothergeneral embodiment of the present invention, and shown in a contractedcondition;

FIGS. 10A-10C illustrate one embodiment of a method for loading thestent of the invention into the proximal end of a catheter;

FIGS. 11A-11C illustrate another embodiment of a method for loading thestent of the invention into the proximal end of a catheter; and

FIGS. 12A-12D illustrate steps in the use of the stent in treating aneuroaneurysm, in accordance with the method of the invention.

DETAILED DESCRIPTION OF THE INVENTION

The present invention includes, in one aspect, a stent adapted foradvancement through a catheter in a upstream to downstream direction toa target vessel site, in a contracted stent condition, and expulsionfrom the catheter, downstream end first, and radial expansion at thetarget site, to engage the walls of the vessel. The stent is formed of acontinuous helical ribbon formed of a preferably shape-memory alloy, andhas a bending-stiffness gradient along its length due to (i) a gradientof ribbon width, (ii) a gradient of ribbon thickness, and/or (iii) agradient of size or number of openings formed in the stent ribbon. Thestent is preferably graftless, i.e., it consists of a metal coil alonewithout a woven or film-like graft formed over the coil or between thecoil windings, and is preferably formed of a shape-memory alloy, asdiscussed below.

By bending-stiffness gradient is meant a difference in bendingstiffness, as measured by amount or degree of stent bending away fromits long axis per force applied; that is, a region of lesser bendingstiffness in the stent will exhibit greater bending in response to agiven force applied in a direction normal to the stent long axis than aregion of greater bending stiffness. In general, and in a preferredembodiment, the stiffness gradient is in a direction of decreasingstiffness on progressing from upstream to the downstream end of thestent, that is, from the more proximal to the more distal stent end,with the stent placed in a catheter. The stiffness gradient may bediscontinuous, meaning that the gradient is formed of two of moresegments of substantially uniform stiffness, or may be continuous alongthe length of the stent.

Aspects of the invention will be illustrated by non-limiting embodimentshaving variable ribbon width (FIGS. 1-5), thickness (FIGS. 6 and 7),number of openings (FIG. 8) in the ribbon wall, or a combination ofthese features (FIG. 9).

FIG. 1 is a side view of one embodiment of a stent 10 in accordance withthe invention and is composed of a continuous helical ribbon, e.g., acoil, comprising a flat, thin and biocompatible material, such as apolymer or metal, having thermal shape memory. Stent 10 incorporatesnon-uniform helical winding widths in a continuous helical ribbon havingan upstream portion 12 and a downstream portion 14.

In the stent 10, these portions are the same length. In otherembodiments, the downstream portion can comprise from about ⅗ to ⅘ ofthe total length. The stent can have a gradient of ribbon widths, withgreater to lesser widths progressing in an upstream-to-downstreamdirection. For example, the ribbon widths can be substantially uniformover the upstream half of the stent 10 shown at 12, and decreasesubstantially uniformly over the downstream half of the stent as shownat 14. In a typical embodiment the upstream ribbon width is about 50mils, decreasing in increments of 10 mils at every other winding, downto about 10 mils in the downstream region of the stent. The downstreamportion can comprise a region of reduced winding width which decreasessubstantially uniformly over the downstream half of the stent.

Preferably, the width, indicated by arrow 16, of the ribbon windings inthe upstream portion is at least ten times, and more preferably at least25 times, the ribbon thickness as indicated at 20. Preferably the ribbonwidth in the upstream portion is at least two times the width in thenarrowest winding in the downstream portion. In stent 10, for example,the ribbon width 16 in the upstream portion 12 is at least two times thesmallest ribbon width 17 in the downstream portion.

The ribbon widths in the upstream portion can be between 25 and 75 mils,and the smallest winding width in the downstream portion can be between5 and 15 mils. In the embodiment shown (FIG. 3), the thickness 20 isconstant along the length of the stent. The ribbon thickness ispreferably between about 0.5 and 2 mils.

The ribbon is capable of existing in a contracted condition (FIG. 1) anda radially expanded condition (FIG. 4). The diameter in the contractedcondition as indicated by arrow 22 can be between about 10 and 30 mils.The diameter of the fully expanded condition can be between about 40 and125 mils.

The stent can be manufactured to have a length and diameter which aresuitable for a particular therapeutic application. For example, thelength in the contracted condition can be between about 50 mm to 100 mm.

In general, the ratio of the length of the stent in the contractedcondition divided by the length in the expanded condition (L_(c)/L_(e))will be approximately equal to the ratio of diameter of the stent in theexpanded condition divided by the diameter in the contracted condition(D₁₀/d₁₀). Thus, a stent having a length of 50 mm and a diameter of 0.5mm in a contracted condition will expand to a length of 10 mm and adiameter of 2.5 mm.

In another aspect of the invention, the stent can include one or moreregions of lesser ribbon width intermediate the ends of the stent. Forexample, the stent 30 comprises non-uniform helical winding widths in acontinuous helical ribbon with regions of greater and lesser ribbonwidths interspersed with one another and includes regions of greaterribbon width shown at 32,36,38 and regions of lesser ribbon width shownat 34,37 and at the downstream end 39. For use in treating a lesion in anarrow and tortuous vessel, such as a neurovascular lesion, the ribbonthickness can be between 0.5 and 2 mils, the greater ribbon width can bebetween 25 and 75 mils, and the lesser ribbon width can be between 5 and15 mils. Stent 30 can be manufactured by laser cutting of a nitinolhypotube, and can include openings as described hereinabove.

The wall of the stent can include a plurality of openings disposed alongthe length of the helical ribbon. The shape of the openings can beround, oval, square, rectangular, diamond, hexagon, or polygon, and thenumber, size, shape of openings can be varied. A preferred opening is acrossed-beam shape such as an “X”, “+”, “Z”, or “I” shape. Preferably,each opening has one beam axis substantially transverse to thelongitudinal axis of the contracted stent. One beam can be alignedtransversely to the other. An example of a shape for the opening isillustrated at 17 in FIG. 1. The openings are “I” shaped whose “I” axisis substantially transverse to the longitudinal axis of the contractedstent. Another example of a suitable opening is shown in FIG. 2 whichincludes a modified “Z” shaped opening. In FIG. 2, the angle θ betweenan elongated central portion 15 and a terminal crossed-beam 18 is about135° C. The openings can be formed using conventional metal workingprocesses such as die and punch, laser cutting, or chemical etching.

In still another aspect, the stent can incorporate uniform helicalwinding widths in a continuous helical ribbon having portions which havedifferent densities of openings, i.e., different numbers and or sizes ofopenings per unit length. The preferred shape of the openings includethose described hereinabove. In an exemplary stent 60, having uniformhelical winding widths (FIG. 8), the density of openings increases fromthe upstream toward the downstream direction. In other embodiments,certain regions having low density of openings can be interspersed withregions having higher density of openings. In still other embodiments,certain regions can lack openings, while adjacent portions includeopenings. The thickness of the stent 60 is constant along the length(FIG. 8). The ribbon thickness is preferably between about 0.5 and 2mils. The stent can be made from a shape-retaining metal alloy using themanufacturing methods described herein.

In still another aspect, the stent can incorporate non-uniform wallthickness in a continuous helical ribbon as exemplified by stent 40(FIGS. 6 and 7). The stent 40 has uniform winding widths, preferablybetween 25 and 75 mils, along the length of the ribbon. The stentincludes an upstream portion 42 and a downstream portion 44, which arethe same length in this embodiment. In other embodiments, the downstreamportion can comprise from about ⅗ to ⅘ of the total length.

Preferably, the width as indicated by arrow 50 of the ribbon windings inthe upstream portion is at least ten times, and more preferably at least25 times, the ribbon thickness indicated by arrows 46. In a preferredembodiment, the ribbon thickness, indicated at 46, in the upstreamportion is at least about two times the smallest ribbon thickness,indicated at 48, in the downstream portion. For example, the ribbonthickness in the upstream portion can be between 1 and 4 mils, and thesmallest winding width in the downstream portion can be between 0.5 and2 mils. The upstream portion can comprise a region of constant windingthickness. The downstream portion can comprise a region of reducedwinding thickness which decreases substantially uniformly over thedownstream half of the stent. In a typical embodiment, the upstreamribbon thickness is about 2 mil, decreasing in increments of about 0.5mils at each winding in the downstream region to final thickness ofabout 0.5 mil. In an alternative embodiment, the winding thickness candecrease substantially uniformly over the whole length of the stent,from the upstream end to the downstream end. The stent 40 can includeopenings, and preferably crossbeam openings, as described hereinabove.

In order to form a stent having variations in wall thickness asdescribed herein, the hypotube is subjected to centerless grinding to awall thickness which tapers at one end, for example, having a wallthickness of 2 mil at the upstream portion 42 to about 0.5 mil at thedownstream portion 44. The remaining manufacturing steps are asdescribed herein.

In yet another aspect, the stent can incorporate along its length,combinations of more than one of the features as described herein ofvariable winding width, thickness, or density of openings. For example,the stent 70 (FIG. 9) includes both decreasing winding widths toward thedownstream end and also an increase in density of openings toward thedownstream end.

The stent preferably exhibits a relatively high degree ofbiocompatibility since it is implanted in the body. Suitable materialsfor the stent include ELGILOY (available from Carpenter TechnologyCorporation of Reading, Pa.) and PHYNOX (available from Metal Imphy ofImphy, France). Both of these metals are cobalt-based alloys which alsoinclude chromium, iron, nickel and molybdenum. Other materials for aself-expanding stent include 316 stainless steel and MP35N alloy whichare available from Carpenter Technology Corporation and Latrobe SteelCompany of Latrobe, Pa., and superelastic Nitinol nickel-titanium alloywhich is available from Shape Memory Applications of Santa Clara, Calif.Nitinol alloy contains about 45% titanium.

In one general embodiment, the shape-memory alloy has a final austentitetransition temperature of between about 25° C. and 37° C. This featureallows the stent to be moved through the catheter in a stress-inducedmartensitic or superelastic state, and assume its preformed, austeniticshape when expelled from the catheter by removing the stress imposed onthe stent by the inner catheter wall and causing the now unstressedstent to transform from stress-induced martensite into austentite andthus regaining its austentitic shape. In another embodiment, theshape-memory alloy has a transition temperature M_(d) greater than 37°C. below which the alloy retains sufficient stress-induced martensiticproperty to allow placement of the stent at or above its A_(f). In otherwords, this allows the stent to be moved through the catheter in astress-induced martensitic (SIM) state, and recover its preformed,austentitic shape when released from the constraints of the catheter, ata temperature that may be substantially above the final austentitetemperature without significant plastic, or otherwise permanentdeformation. In this embodiment, the final austentite temperature may bequite low, e.g., 4° C., or it may be room temperature of higher.

Nitinol cylindrical tubes having a final austentitic temperature betweenabout 25° C. and 45° C., preferably about 25° C. and 37° C., can beprepared according to known methods. In an exemplary method ofmanufacture of the stent having these properties, a nitinol hypotube,e.g., 8 mil wall thickness, is subjected to centerless grinding to awall thickness of 3 mil. The stent pattern is cut by a laser (e.g., asdescribed by Madou in Fundamentals of Microfabrication, CRC Press,1997). Both inner and outer surfaces are polished to a mirror finishusing electro-polish techniques (e.g., as described by Madou, 1997). Agold coat is applied by ion beam assist.

During manufacture, the ribbon is formed at the expanded condition (FIG.4), corresponding to the final deployed size (e.g., about 2-4 mm outerdiameter), and heated to a temperature above the transition temperature.The ribbon is then subjected to thermoelastic martensitic transformation(e.g., as described in U.S. Pat. No. 5,190,546 incorporated by referencein its entirety herein) by cooling below the transition temperaturerange of the alloy and deformation to the contracted condition suitablefor use within an intraluminal catheter. For example, the stent can berolled using a rod having a notch at one end which engages thedownstream end of the stent. The transition temperature can be modifiedby varying the ratios of each metal in the alloy and in the presentinvention preferably is within the range between about 25° C. to 45° C.at which the stent expands. A more preferred transition temperaturerange is between about 25° C. to 37° C. For example, the alloy cancomprise 55% nickel, and 45% titanium which gives a transitiontemperature of about 32° C. to 33° C., which is below body temperaturebut above room temperature.

Nitinol cylindrical tubes having a martensite temperature M_(D) belowwhich the alloy can assume a stress-induced martensitic condition whilebeing stressed to the extent necessary to place or otherwise use thedevice, of greater than about 37° C., preferably greater than about 40°C., are also prepared according to known methods, e.g., U.S. Pat. No.4,505,767. For example an ideal alloy would act, at about 37° C., as aconstant force spring over a strain range up to about 5% or more. Thisis a measurement of the degree to which an alloy, at a giventemperature, can be strained in a purely austentitic state by theformation of stress-induced martensite without significant plasticdeformation. In other words, the strain caused by the application of agiven stress at a given temperature is substantially recoverable. Inpractice, the maximum stress realized occurs sometime during the processof placing a nitinol device at a given temperature. Accordingly, asuitable alloy will provide a device that is capable of substantiallyrecovering its austentitic shape without significant plasticdeformation, upon placement in the body.

The operation of the stent of the invention will now be discussed inreference to device 10 for the sake of clarity, and not by way oflimitation, it being appreciated that any other embodiment can be usedin the same manner.

The helical stent is loaded into a catheter as illustrated in FIGS.9A-9C. The catheter and loaded stent form a device in accordance withanother aspect of the invention. The device may additionally include apusher wire for advancing the stent through the lumen of the catheter,as described below.

Prior to loading, the stent can be retained in a contracted condition,e.g. within a cartridge 80. The stent can be wrapped around a mandrel(not represented) prior to placement within the cartridge. Thedownstream end of the stent is loaded into hub 84 of a delivery systemsuch as a catheter 86. Depression of plunger 88 pushes the stent fromits holding chamber 90 into the distal end 92 of the cartridge. A pusherwire 94 is then introduced into the hub of the catheter. The inner wallof the downstream end of the stent frictionally engages end ball 96mounted to the distal end of the pusher wire 94. The pusher wire is thenpushed downstream through the catheter in order to advance the stent, ina contracted condition, to the target site. Thus, the stent is draggedthrough the catheter by the end ball near the tip which drags the stentnear (but not at) its downstream end.

Another method for loading the stent into a catheter uses a pusher wire180 having a distal notch 182 adapted to hold the downstream end of thestent as illustrated in FIGS. 11A-11C. The wire can have more than onenotch along its length for attachment to more than one location on thestent (not illustrated). With the stent at a temperature below thetransition temperature, the pusher wire 180 is rotated along itslongitudinal axis to wind the stent to its contracted condition. Thestent is manually inserted into and retained within a retaining sleeve184. An example of a suitable sleeve is a 15-20 cm section of polymericmicrocatheter (Target Therapeutics, Freemont, Calif.). The sleeve ispositioned at the opening of the hub 186 of catheter 188 and the stentis advanced in its contracted state from the sleeve and into thecatheter (as indicated by arrow 190) using the pusher wire.

In another aspect of the invention, the stent is used in the treatmentof a variety of vascular lesions. This aspect will be illustrated inFIGS. 12A-12D using stent 10 of the invention in a method for treating aneurovascular aneurysm. In accordance with the method, a catheter 86 isguided within the lumen 100 of a vessel 102 to the lesion site usingfluoroscopy and standard angiographic techniques (FIG. 12A). Preferablythe pusher wire 94 is held steady and the catheter is retracted in anupstream direction, as indicated by arrow 106 to partially release thestent 10 downstream end first (FIG. 12B).

During release from the catheter, the stent is “naked” and free-moving;that is, it is not mounted on a balloon, constrained by a sheath, orheld in place by a tethering wire. The stent does not deploy whilepartially outside of the catheter (FIG. 12B) and can be repositioned orremoved as desired.

During the final stage of deployment, the pusher wire is held steady,and the catheter is retracted, as shown by arrow 106, to fully expel thestent (FIG. 12B). Warming of the stent to body temperature at the targetsite causes the stent to expand radially against the vessel walls at thetarget site. The expansion causes release of the end ball, allowingwithdrawal of the pusher wire, as shown by arrow 108 (FIGS. 12C, 12D) tocomplete the procedure. The stent deploys once it is completely outsidethe catheter (FIG. 12D).

When using a pusher wire having a terminal notch, the pusher wire ispushed downstream through the catheter in order to advance the stent, ina contracted condition, to the target site. The stent disengages thenotch upon deployment at the target site (not shown).

When used in the treatment of an aneurysm, for example, a highpercentage of surface area coverage is needed to effectively cover themouth 110 of the aneurysm 112 (FIG. 12A). A preferred helical ribbon ofthe invention is effective to cover between 50% and 80%, and preferablybetween 65% and 80%, of the surface area of the vessel region containingthe fully expanded stent. The length of the stent is selected so that inthe expanded state, it extends beyond both sides of the mouth of theaneurysm.

The stent of the present invention can be used in the treatment of avariety of vascular lesions such as an aneurysm, fistula, occlusion, ornarrowing and is useful in treating targets located in tortuous andnarrow vessels, for example in the neurovascular system, or in certainsites within the coronary vascular system, or in sites within theperipheral vascular system such as superficial femoral, popliteal, orrenal arteries.

As described herein, the stent incorporates longitudinal gradients ofstructural features to achieve the flexibility, rate of radial expansionfrom a contracted to an expanded state, coverage of void space, andradial strength which are desired for its intended use. For example, asdescribed herein, the ribbon width can be selected during manufacture.In a particular example, stent 10 is substantially cylindrical in bothits contracted and expanded conditions. However, during the initialstages of deployment, the greater ribbon width along the upstreamportion of the stent promotes slower expansion after the stent isreleased form the catheter, relative to the expansion of a stent havinguniform winding widths equal to a smallest winding width in thedownstream portion. The slower expansion advantageously reduces the riskof trauma to the vessel wall. The greater ribbon width gives moresurface coverage of the vessel wall and also provides more uniformapposition against the wall which lowers hemodynamic turbulence andlowers the risk of vascular thrombosis.

In general, narrower winding widths confer increased flexibility. Stent10 incorporates downstream portions having relatively lesser ribbonwidths. As compared to a stent having uniform ribbon widths equal to thelargest winding width in the upstream portion, the lessor ribbon widthsprovide a decrease in stiffness to the stent which increases the angleof bend through which the stent can be advanced in a contractedcondition. This is especially important for advancing the stent within acatheter positioned within a tortuous vessel. Higher flexibility alsoallows the stent to conform to vessel curvature at the target site.Stent 30 includes intermediate portions having lessor winding widths,which also increase the flexibility of the stent.

Likewise, the ribbon thickness can be varied as in stent 40, withgreater thickness generally slower rate of expansion above thetransition temperature, and greater radial strength, as compared tothinner ribbon windings. Thinner winding widths generally conferincreased flexibility. Stent 40 incorporates downstream portions havingrelatively lesser ribbon thickness. As compared to a stent havinguniform ribbon thickness equal to the largest winding width in theupstream portion, the lessor ribbon thickness provides a decrease instiffness to the stent which increases the angle of bend through whichthe stent can be advanced in a contracted condition. This is especiallyimportant for advancing the stent within a catheter positioned within atortuous blood vessel. Higher flexibility also allows the stent toconform to vessel curvature at the target site. It will be recognizedthat a stent can include intermediate portions having lessor windingthickness, in analogy with stent 30, which can also increase theflexibility of the stent.

As described herein, the ribbon wall of the stent can incorporateopenings. The shape, orientation, and size of the openings can beselected during manufacture. The density of openings can influence theradial strength of the stent, the rate of expansion, the flexibility andthe area of surface coverage. Different portions of a stent can havedifferent density of openings, or different sizes and shapes ofopenings, as shown in FIGS. 7 and 8. Greater density of openings inribbon windings generally gives greater flexibility.

Stent 60, for example, incorporates downstream portions havingrelatively greater density of openings. As compared to a stent havinguniform density of openings along the ribbon equal to the lowest densityof openings in the upstream portion, the higher density of openingsprovides a decrease in stiffness to the stent which increases the angleof bend through which the stent can be advanced in a contractedcondition. This is especially important for advancing the stent within acatheter positioned within a tortuous vessel. A stent can includeintermediate portions having regions of higher or lower density ofopenings which can also increase the flexibility of the stent.

Applicant has determined that a shape which incorporates a“crossed-beam” opening disposed along the length of the helical ribbon,where each opening has at least one beam axis substantially transverseto the longitudinal axis of the stent, has the advantage of facilitatingthe bending of a stent, in the contracted condition, in both a directionlongitudinal to the axis of the stent and in a direction transverse tothe longitudinal axis of the stent. For a stent in the expandedcondition, such openings minimize the size of the opening, to givegreater surface coverage, while maximizing the radial strength of thestent. An example of a preferred opening is an I-beam shaped openinghaving the “I” axis transverse to the longitudinal axis of the stent inthe contracted condition. Another example is a “Z” shaped opening wherethe central portion of the “Z” is linearly extended and is transverse tothe longitudinal axis of the stent in the contracted state.

The size and shape of the openings can be varied to increase or decreasethe contact area between the stent and the vessel wall. The openings andthe spacing between adjacent ribbon windings contribute to void spacewhich is needed to promote efficient endothelial-cell growth on andaround the stent. A void space of about 15% to 50% is preferred.

It will be appreciated that the present invention provides a stenthaving a variety of features which can be varied during themanufacturing process in order to optimize the structure of the stentfor its intended use. More than one feature, such as width, thickness,or shape or density of openings can be combined, to achieve desiredflexibility, rate of expansion, or area of surface coverage. Forexample, stent 70 incorporates variations in both helical windingswidths and density of openings.

In the process of manufacture, the stent of the invention preferablyincludes thin wall construction which contributes to greater lumendiameter in the stent region, and minimizes blood flow turbulence at theupstream edge of the stent, thereby reducing the risk of blood clotting.

The stent preferably is manufactured to minimize adverse effects, suchas thrombosis, which can occur during use such as a result ofhemodynamic turbulence, internal hyperplasia, and reaction to a foreignbody. For example, the manufacturing processes includes anelectro-polishing step to give the stent a mirror finish a gold coatingstep to improve biocompatibility.

A variety of other modifications can also be made. For example, thestent can be coated to enhance radiopacity, such as by using gold oranother radiopaque metal. It can be coated with drugs or chemical agentsto promote faster and more complete clotting of the aneurysm sac, tominimize the thromobogenicity of the stent in the artery, and to provideother functions. It can be covered with an autologous or syntheticgraft, or coated to fill the void areas of the stent.

All publications and patent applications cited in this specification areherein incorporated by reference as if each individual publication orpatent application were specifically and individually indicated to beincorporated by reference.

Although the foregoing invention has been described in some detail byway of illustration and example for purposes of clarity ofunderstanding, it will be readily apparent to those of ordinary skill inthe art in light of the teachings of this invention that certain changesand modifications may be made thereto without departing from the spiritor scope of the appended claims.

1. A method of treating a lesion at a neurovascular target vessel site,comprising guiding a neuro-interventional catheter to the target site,advancing through the catheter, a stent adapted for advancement througha catheter in an upstream to downstream direction to the target site ina contracted stent condition and with expulsion form the catheter,downstream end first, and radial expansion at the target site, to engagethe walls of the vessel, Said stent having a bending-stiffness gradient(define) along its length due to one or more of the following: (i) agradient of ribbon width; (ii) a gradient of ribbon thickness; (iii) agradient of size or number of openings formed in the stent ribbon andexpelling the stent from the catheter at the target site, causing thestent to expand radially against the vessel walls at the target site. 2.The method of claim 1, wherein said guiding includes engaging a pusherwire with the stent, pushing the stent through the catheter with thepusher wire, and expelling the stent from the catheter at the targetsite, with stent radial expansion at the target site being effective torelease the stent from the pusher wire.
 3. The method of claim 2,wherein the stent wherein the stent is relasably attached to the pusherwire, for release therefrom, when the stent is released and extands toits expanded condition.
 4. The method of 1, wherein the stent has acontracted-condition diameter of Between about 10 and 30 mils, and adiameter in a fully expanded condition of between 40 and 125 mils. 5.The method of claim 1, wherein the stiffness gradient in the stent isdue to a gradient of ribbon width, lesser ribbon width at the upstreamend of the stent, and greater ribbon width at the downstream end of thestent, where the greater ribbon width is (i) at least ten times theribbon thickness and (ii) at least two times the lesser width, saidgreater ribbon being effective to reduce the rate of expansion of thestent from its contracted to its radially extended condition, relativeto that of a stent having uniform winding widths equal to the lesserribbon widths, said lesser ribbon width being effective to increase theangle of catheter bend through which the catheter can be advanced, in anupstream to downstream direction, relative to that of a stent havinguniform winding widths equal to the greater ribbon width.
 6. The methodof claim 5, wherein the stent ribbon thickness is between 0.5 and 2mils, the greater ribbon width is between 25 and 75 mils, and the lesserribbon width is between 5 and 15 mils.
 7. The method of claim 1, whereinthe stent openings are I-beam shaped openings whose “I” axis is alignedtransversely to the longitudinal axis of the stent in the contractedstate, or Z-shaped openings whose central axis is aligned transverselyto the longitudinal axis of the stent in the contracted state.
 8. Themethod of claim 1, wherein the stent helical ribbon is effective tocover between 50% and 80% of the surface area of the vessel regioncontaining the stent.